Stimulator systems and methods for obstructive sleep apnea

ABSTRACT

An electrode lead comprises an electrically insulative cuff body and at least three axially aligned electrode contacts circumferentially disposed along the inner surface of the cuff body when in the furled state. The electrode contacts may be circumferentially disposed around a nerve, and an electrical pulse train may be delivered to the electrode contacts thereby stimulating the nerve to treat obstructive sleep apnea. The electrical pulse train may be one that pre-conditions peripherally located nerve fascicles to not be stimulated, while stimulating centrally located nerve fascicles. A feedback mechanism can be used to titrate electrode contacts and electrical pulse train to the patient. A sensor that is affixed to the case of a neurostimulator can be used to measure physiological artifacts of respiration, and a motion detector can be used to sense tapping of the neurostimulator to toggle the neurostimulator between an ON position and an OFF position.

RELATED APPLICATION DATA

This application is a continuation of U.S. patent application Ser. No.16/245,509, filed Jan. 11, 2019, entitled “STIMULATOR SYSTEMS ANDMETHODS FOR OBSTRUCTIVE SLEEP APENA,” which is a continuation of U.S.patent application Ser. No. 15/885,618, filed Jan. 31, 2018, whichclaims the benefit of U.S. Provisional Patent Application 62/453,311,filed Feb. 1, 2017. The contents of the aforementioned patentapplications are hereby expressly incorporated by reference in theirentirety.

FIELD OF THE INVENTION

The present invention relates to systems and methods for the treatmentof obstructive sleep apnea (OSA).

BACKGROUND

OSA is a highly prevalent sleep disorder that is caused by the collapseof or increase in the resistance of the pharyngeal airway, oftenresulting from tongue obstruction. The obstruction of the upper airwayis mainly caused by reduced genioglossus muscle activity during thedeeper states of NREM sleep. Obstruction of the upper airway causesbreathing to pause during sleep. Cessation of breathing causes adecrease in the blood oxygen saturation level, which is eventuallycorrected when the person wakes up and resumes breathing. The long-termeffects of OSA include high blood pressure, heart failure, strokes,diabetes, headaches, and general daytime sleepiness and memory loss,among other symptoms.

OSA is extremely common, having a similar prevalence as diabetes orasthma. Over 100 million people worldwide suffer from OSA, with about25% of those being treated. Continuous Positive Airway Pressure (CPAP)is the usual established therapy for people who suffer from OSA. Morethan five million patients own a CPAP machine in North America, but manydo not comply with use of these machines, because they cover the mouthand nose and, hence, are cumbersome and uncomfortable.

The use of neurostimulators to open the upper airway has been exploredby several companies as a treatment for alleviating apneic events. Suchtherapy involves stimulating the nerve fascicles of the hypoglossalnerve (HGN) that innervate the intrinsic and extrinsic muscles of thetongue in a manner that prevents retraction of the tongue, which wouldotherwise close the upper airway during inspiration of the respiratorycycle.

ImThera Medical is currently in FDA clinical trials for a stimulatorsystem that is used to stimulate the trunk of the HGN with a nerve cuffelectrode. The stimulation system does not provide a sensor or sensing,and therefore, the stimulation delivered to the HGN trunk is notsynchronized to the respiratory cycle. Thus, the tongue and othermuscles that are innervated by nerve fascicles of the HGN trunk arestimulated irrespective of the respiratory cycle.

The rationale for this treatment method appears to be that it is enoughsimply to tone the tongue muscle and other nearby muscles, so that thetongue muscle does not retract in a manner that would cause OSA. Thebelief is that it is not necessary to specifically target theprotraction (i.e., anterior movement) of the tongue muscle and tosynchronize the occurrence of tongue protraction when it is most needed,i.e., during inspiration. The nerve cuff electrode of the ImTheraMedical system has multiple electrode contacts helically surrounding theproximal part of the HGN nerve trunk. So, instead, each electrodecontact delivers stimulation in a sequential order to the HGN trunk. Forexample, if a three-electrode contact nerve cuff is used, electrodecontact #1 stimulates, then stops, electrode contact #2 stimulates, thenstops, electrode contact #3 stimulates, then stops, then electrodecontact #1 stimulates, then stops and so on. Since all or most electrodecontacts deliver stimulation, there is no selection process to choosethe best one or two electrode contacts that is finally used to deliverthe best stimulation to alleviate sleep apnea.

A disadvantage of the ImThera Medical system is that it does not targettongue protraction coincident with the inspiration phase of respiration,since it does not have a sensor to enable synchronization of stimulationto the respiratory cycle. Since there is no attempt to synchronize thestimulation with the respiratory cycle, the tongue protraction does notoccur when it would appear to help the most—during inspiration when OSAcan occur. Also, because the HGN trunk contains nerve fascicles thatinnervate muscles other than the muscle that extend the tongue, theImthera Medical method of stimulation at the HGN trunk does not justtarget the specific protrusor muscles of the tongue muscle, but othermuscles that are not targeted. Thus, stimulating the HGN trunk in anarbitrary manner may recruit other nerve fascicles of the HGN trunk thatmay not contribute to the protraction of the tongue.

Another company, Inspire Medical Systems, Inc., does offer a stimulationsystem with a sensor, and therefore does attempt to time the onset ofstimulation to the breathing cycle. This system, which is FDA approvedfor sale in the United States since April 2010, uses a simple, bipolarelectrode (two electrode contacts only) within a nerve cuff electrodeand implants the electrode at the branch of the HGN that is responsiblefor protruding the tongue. A simple, two-electrode contact orthree-electrode contact cuff electrode can be used at the branch nerve,unlike the HGN trunk, because at the distal branch location, the nervefascicles generally innervate the specific tongue protrusor muscle andnot other muscles.

However, implanting the electrode at a branch of the HGN takesadditional surgery time, which increases trauma to the patient andincreases the substantial expense of operating room time. By attachingthe nerve cuff electrode to the proximal section of the main trunk ofthe HGN, compared to placing the nerve cuff electrode at the more distalend of the HGN, it estimated that the surgical time will be reduced byapproximately one hour. Even more importantly, because the branch nerveis small and more difficult to isolate than the HGN trunk, implanting anerve cuff electrode at the branch site demands heightened expertisefrom the otolaryngologist/Ear Nose and Throat (ENT) surgeon orneurosurgeon, which significantly increases the chance for error andsurgical risks. Furthermore, because the distal location of the HGN hasa smaller diameter of nerves, and hence the required electrodes need tobe smaller, the smaller nerve cuff electrode may be more difficult tomanufacture.

Thus, it is certainly desirable to implant the nerve cuff electrode atthe trunk of the hypoglossal nerve. However, one must then deal with thefact that the target nerve fascicles may be near the center of the nervetrunk and are not easily isolated and stimulated, while at the same timeavoiding stimulating other non-targeted fascicles in the same nervetrunk.

Furthermore, a pressure sensor is connected to neurostimulator of theInspire system by a lead, thereby allowing the pressure sensor to beplaced remotely from the implanted site of the neurostimulator. However,the fact that the pressure sensor has a lead connected to the stimulatornecessitates some additional surgery, because the sensor lead is anotherappendage that must be implanted.

There, thus, remains a need for improved systems and methods forselectively recruiting only the fascicles of the hypoglossal nerve insynchronization with the respiratory cycle for treating OSA of apatient, while minimizing the surgery time and effort required toimplant the neurostimulation components in the patient.

SUMMARY

In accordance with a first aspect of the present inventions, anelectrode lead comprises an elongated lead body having a proximal endand a distal end, and at least three connector contacts affixed to theproximal end of the lead body. In one embodiment, the lead body has atleast one portion that is S-shaped to provide strain relief. Theelectrode lead further comprises a biologically compatible, flexible,electrically insulative cuff body affixed to the distal end of the leadbody. The cuff body is pre-shaped to transition from an unfurled stateto a furled state, wherein the cuff body, when in the furled state hasan inner surface for contacting a nerve. In one embodiment, the innersurface of the furled cuff body has a diameter in the range of 2.5 mm to4.0 mm. In another embodiment, the cuff body is self-adjusting, suchthat the cuff body accommodates different sized nerve diameters, anddiameter changes over time.

The electrode lead further comprises at least three axially alignedelectrode contacts circumferentially disposed along the inner surface ofthe cuff body when in the furled state, and at least three electricalconductors extending through the lead body respectively between the atleast three connector contacts and the electrode contacts. In oneembodiment, when the cuff body is in the furled state, the electrodecontacts circumferentially span at least a 180-degree arc around theinner surface of the cuff body. In another embodiment, when the cuffbody is in the furled state, the electrode contacts circumferentiallyspan at least a 270-degree arc around the inner surface of the cuffbody. In still another embodiment, when the cuff body is in the unfurledstate, a center-to-center spacing of each pair of adjacent ones ofelectrode contacts is equal to or less than twice the width of eachelectrode contact of the respective pair of electrode contacts.

A neurostimulation system may comprise the electrode lead describedabove, and a neurostimulator comprising a connector configured forreceiving the proximal contacts of the electrode lead, stimulationcircuitry configured for generating an electrical pulse train, andcontrol circuitry configured for causing the stimulation circuitry todeliver the electrical pulse train to at least one of the electrodecontacts of the electrode lead. A method of using the electrode leaddescribed above may comprise maintaining the cuff body in the unfurledstate while placing the cuff body in contact with the nerve, placing thecuff body from the unfurled state into the furled state, such that thecuff body wraps around the nerve, and delivering an electrical pulsetrain to at least one of the electrode contacts of the electrode lead,thereby stimulating the nerve.

In accordance with a second aspect of the present inventions, aneurostimulation system comprises an electrode lead having a lead body.In one embodiment, the lead body has at least one portion that isS-shaped to provide strain relief. The electrode lead further comprisesa biologically compatible electrically insulative cuff body affixed tothe distal end of the lead body. The cuff body is pre-shaped andflexible to transition from an unfurled state to a furled state. Thecuff body, when in the furled state has an inner surface for contactinga nerve. In one embodiment, the inner surface of the furled cuff bodyhas a diameter in the range of 2.5 mm to 4.0 mm. In another embodiment,the cuff body is self-adjusting, such that the cuff body accommodatesdifferent sized nerve diameters, and diameter changes over time.

The electrode lead further comprises at least three axially alignedelectrode contacts circumferentially disposed along the inner surface ofthe cuff body when in the furled state. In one embodiment, when the cuffbody is in the furled state, the electrode contacts circumferentiallyspan at least a 180-degree arc around the inner surface of the cuffbody. In another embodiment, when the cuff body is in the furled state,the electrode contacts circumferentially span at least a 270-degree arcaround the inner surface of the cuff body. In still another embodiment,when the cuff body is in the unfurled state, a center-to-center spacingof each pair of adjacent ones of electrode contacts is equal to or lessthan twice the width of each electrode contact of the respective pair ofelectrode contacts.

The neurostimulation system further comprises a neurostimulatorconfigured for delivering an electrical pulse train to at least one ofthe electrode contacts of the electrode lead. By way of example, theelectrical pulse train may have an initial, preconditioning current orvoltage amplitude and a subsequent higher stimulating current or voltageamplitude. In one embodiment, the electrode contacts comprise a pair ofadjacent ones of the electrode contacts, and the neurostimulator isconfigured for delivering the electrical pulse train between the pair ofadjacent ones of the electrode contacts in a bipolar mode. In anotherembodiment, the neurostimulator is further configured for sensingphysiological artifacts that are caused by respiration, and deliveringthe electrical pulse train to the electrode contacts in synchronizationwith a respiratory cycle based on the sensed physiological artifacts. Asone example, the neurostimulator may be configured for determining thenext projected onset of an inspiratory phase of the respiratory cyclebased on the sensed physiological artifacts, and delivering theelectrical pulse train to the at least one electrode contact immediatelybefore, at, or right after the next projected onset of the inspiratoryphase of the respiratory cycle. In another embodiment, theneurostimulator is configured for storing data representative of thephysiological artifacts sensed by the sensing circuitry.

The neurostimulation system may optionally comprise a clinicianprogrammer configured for selecting the electrode contacts, andtranscutaneously communicating with the neurostimulator, and programmingthe neurostimulator to deliver the electrical pulse train to theselected electrode contact; a patient programmer configured fortranscutaneously communicating with the neurostimulator, and togglingthe neurostimulator between an OFF position and an ON position, suchthat in the OFF position, no stimulation is delivered; and/or anexternal charger configured for inductively and transcutaneouslycharging the neurostimulator.

The neurostimulation system may optionally comprise a feedback mechanismconfigured for measuring a physiological parameter of the patientindicative of the efficacy of the delivered electrical pulse train intreating obstructive sleep apnea of a patient. As examples, the feedbackmechanism may comprise one or more temperature sensors configured formeasuring the temperature of inhaled and exhaled air of a patient, oneor more carbon dioxide (CO2) sensors configured for measuring aconcentration of CO2 in inhaled and exhaled air of the patient, one ormore electro-myographic (EMG) sensors configured for measuring theelectrical potential generated by the muscle cells of a tongue of thepatient, one or more cameras configured for capturing pictures of theairway of the patient, or one or more inertial sensors configured formeasuring the movement of the tongue of the patient. If theneurostimulation system comprises a clinician programmer, it can beconfigured for computing a score of the at least one electrode based onthe measured physiological parameter.

In accordance with a third aspect of the present inventions, a method ofstimulating a nerve (e.g., a trunk of a hypoglossal nerve (HGN)) of apatient to treat an ailment (e.g., obstructive sleep apnea (OSA)comprises circumferentially disposing at least three axially alignedelectrode contacts around the nerve (e.g., on the HGN trunk proximal toa medical branch of the HGN trunk). In one method, the nerve has adiameter in the range of 2.5 mm to 4.0 mm. In another method, theelectrode contacts circumferentially span at least a 180-degree arcaround nerve. In still another method, the electrode contactscircumferentially span at least a 270-degree arc around the nerve. Inyet another method, a center-to-center spacing of each pair of adjacentones of electrode contacts is equal to or less than twice the width ofeach electrode contact of the respective pair of electrode contacts.

The method further comprises delivering an electrical pulse train to atleast one of the electrode contacts, thereby stimulating the nerve totreat the ailment. The electrode contacts may comprise a pair ofadjacent ones of the electrode contacts, and the electrical pulse trainis delivered between the pair of adjacent ones of the electrode contactsin a bipolar mode. In one exemplary method, the electrical pulse trainhas an initial, preconditioning current or voltage amplitude and asubsequent higher stimulating current or voltage amplitude, such thatone or more peripherally located nerve fascicles in the nerve arepre-conditioned by the initial preconditioning current or voltageamplitude, and one or more centrally located nerve fascicles in thenerve further away from the at least one electrode than the peripherallylocated nerve fascicles are triggered by the higher stimulating currentor voltage amplitude, while the one or more pre-conditioned peripherallylocated nerve fascicles are not triggered by the higher stimulatingcurrent or voltage amplitude.

An optional method further comprises sensing physiological artifactsthat are caused by respiration, and delivering the electrical pulsetrain to the electrode contacts in synchronization with a respiratorycycle based on the sensed physiological artifacts. As one example, themethod may further comprise determining the next projected onset of aninspiratory phase of the respiratory cycle based on the sensedphysiological artifacts, and delivering the electrical pulse train tothe electrode contacts immediately before, at, or right after the nextprojected onset of the inspiratory phase of the respiratory cycle. Themethod may further comprise storing data representative of the sensedphysiological artifacts.

Another optional method further comprises measuring a physiologicalparameter of the patient indicative of the efficacy of the deliveredelectrical pulse train in treating an ailment of a patient. As examples,the physiological parameter may comprise one or more of measuring thetemperature of inhaled and exhaled air of a patient, measuring aconcentration of CO2 in inhaled and exhaled air of the patient,measuring the electrical potential generated by the muscle cells of atongue of the patient, capturing pictures of the airway of the patient,and measuring the movement of the tongue of the patient. The method mayfurther comprise computing a score of the at least one electrode basedon the measured physiological parameter.

In accordance with a fourth aspect of the present inventions, anothermethod of stimulating a nerve (e.g., a trunk of a hypoglossal nerve(HGN)) of a patient to treat an ailment (e.g., obstructive sleep apnea(OSA) comprises disposing at least one electrode contact adjacent thenerve (e.g., on the HGN trunk proximal to a medical branch of the HGNtrunk), and delivering an electrical pulse train to the electrodecontact(s), thereby treating the ailment. The nerve has one or moreperipherally located nerve fascicles and one or more centrally locatednerve fascicles further away from the electrode contact(s) than theperipherally located nerve fascicles, and electrical pulse train has aninitial, preconditioning current or voltage amplitude and a subsequenthigher stimulating current or voltage amplitude, such that the one ormore peripherally located nerve fascicles are pre-conditioned by theinitial preconditioning current or voltage amplitude, and the centrallylocated nerve fascicle(s) are triggered by the higher stimulatingcurrent or voltage amplitude, while the one or more pre-conditionedperipherally located nerve fascicles are not triggered by the higherstimulating current or voltage amplitude.

In one method, the nerve has a diameter in the range of 2.5 mm to 4.0mm. In another method, the electrode contact(s) comprises a plurality ofelectrode contacts circumferentially disposed around the nerve. Theelectrode contacts may, e.g., be axially aligned with each other, andmay circumferentially span at least a 180-degree arc around the nerve,or even at least a 270-degree arc around the nerve. In still anothermethod, a center-to-center spacing of each pair of adjacent ones ofelectrode contacts is equal to or less than twice the width of eachelectrode contact of the respective pair of electrode contacts. In stillanother method, the electrode contact(s) comprises a pair of adjacentones of the electrode contacts, and the electrical pulse train isdelivered between the pair of adjacent ones of the electrode contacts ina bipolar mode.

An optional method further comprises sensing physiological artifactsthat are caused by respiration, and delivering the electrical pulsetrain to the electrode contact(s) in synchronization with a respiratorycycle based on the sensed physiological artifacts. As one example, themethod may further comprise determining the next projected onset of aninspiratory phase of the respiratory cycle based on the sensedphysiological artifacts, and delivering the electrical pulse train tothe electrode contact(s) immediately before, at, or right after the nextprojected onset of the inspiratory phase of the respiratory cycle. Themethod may further comprise storing data representative of the sensedphysiological artifacts.

Another optional method further comprises measuring a physiologicalparameter of the patient indicative of the efficacy of the deliveredelectrical pulse train in treating an ailment of a patient. As examples,the physiological parameter may comprise one or more of measuring thetemperature of inhaled and exhaled air of a patient, measuring aconcentration of CO2 in inhaled and exhaled air of the patient,measuring the electrical potential generated by the muscle cells of atongue of the patient, capturing pictures of the airway of the patient,and measuring the movement of the tongue of the patient. The method mayfurther comprise computing a score of the at least one electrode basedon the measured physiological parameter.

In accordance with a fifth aspect of the present inventions, aneurostimulation system for treating obstructive sleep apnea (OSA) in apatient comprises an electrode lead carrying at least one of theelectrode contacts. In one embodiment, the electrode lead comprises alead body, and a biologically compatible, flexible, electricallyinsulative cuff body affixed to distal end of the lead body. In thiscase, the cuff body may be pre-shaped to transition from an unfurledstate to a furled state, the cuff body, when in the furled state has aninner surface for contacting a nerve, and the at least one electrodecontact(s) comprises a plurality of electrode contacts circumferentiallydisposed along the inner surface of the cuff body when in the furledstate. The inner surface of the furled cuff body has a diameter in therange of 2.5 mm to 4.0 mm, the cuff body may be self-adjusting, suchthat the cuff body accommodates different sized nerve diameters, anddiameter changes over time, and the electrode contacts may be axiallyaligned with each other.

In one embodiment, when the cuff body is in the furled state, theelectrode contacts circumferentially span at least a 180-degree arcaround the inner surface of the cuff body. In another embodiment, whenthe cuff body is in the furled state, the electrode contactscircumferentially span at least a 270-degree arc around the innersurface of the cuff body. In still another embodiment, when the cuffbody is in the unfurled state, a center-to-center spacing of each pairof adjacent ones of electrode contacts is equal to or less than twicethe width of each electrode contact of the respective pair of electrodecontacts.

The neurostimulation system further comprises a neurostimulatorconfigured for delivering an electrical pulse train to the electrodecontact(s). By way of example, the electrical pulse train may have aninitial, preconditioning current or voltage amplitude and a subsequenthigher stimulating current or voltage amplitude. In one embodiment, theelectrode contact(s) comprises a pair of adjacent ones of the electrodecontacts, and the neurostimulator is configured for delivering theelectrical pulse train between the pair of adjacent ones of theelectrode contacts in a bipolar mode. In another embodiment, theneurostimulator is further configured for sensing physiologicalartifacts that are caused by respiration, and delivering the electricalpulse train to the electrode contacts in synchronization with arespiratory cycle based on the sensed physiological artifacts. As oneexample, the neurostimulator may be configured for determining the nextprojected onset of an inspiratory phase of the respiratory cycle basedon the sensed physiological artifacts, and delivering the electricalpulse train to the at least one electrode contact immediately before,at, or right after the next projected onset of the inspiratory phase ofthe respiratory cycle. In another embodiment, the neurostimulator isconfigured for storing data representative of the physiologicalartifacts sensed by the sensing circuitry.

The neurostimulation system may optionally comprise a clinicianprogrammer configured for selecting the electrode contacts, andtranscutaneously communicating with the neurostimulator, and programmingthe neurostimulator to deliver the electrical pulse train to theselected electrode contact; a patient programmer configured fortranscutaneously communicating with the neurostimulator, and togglingthe neurostimulator between an OFF position and an ON position, suchthat in the OFF position, no stimulation is delivered; and/or anexternal charger configured for inductively and transcutaneouslycharging the neurostimulator.

The neurostimulation system further comprises a feedback mechanismconfigured for measuring a physiological parameter of the patientindicative of an efficacy of the delivered electrical pulse train intreating the OSA. As examples, the feedback mechanism may comprise oneor more temperature sensors configured for measuring the temperature ofinhaled and exhaled air of a patient, one or more carbon dioxide (CO2)sensors configured for measuring a concentration of CO2 in inhaled andexhaled air of the patient, one or more electro-myographic (EMG) sensorsconfigured for measuring the electrical potential generated by themuscle cells of a tongue of the patient, one or more cameras configuredfor capturing pictures of the airway of the patient, and one or moreinertial sensors configured for measuring the movement of the tongue ofthe patient.

If the neurostimulation system comprises a clinician programmer, it canbe configured for computing a score of the at least one electrode basedon the measured physiological parameter. For example, the clinicianprogrammer may be configured for determining the efficiency of eachinspiration phase in the respiratory cycle based on the measuredphysiological parameter, and computing the score based on the determinedefficiency of each inspiration phase in the respiratory cycle.

In one embodiment, the feedback mechanism comprises one or moretemperature sensors, the measured physiological parameter is apeak-to-peak difference in temperature of inhaled and exhaled air of thepatient, the clinician programmer determines the efficiency of eachinspiration phase in the respiratory cycle based on the measuredphysiological parameter, and computes the score based on the determinedefficiency of each inspiration phase in the respiratory cycle.

In another embodiment, the feedback mechanism comprises one or morecarbon dioxide (CO2) sensors, the measured physiological parameter is apeak-to-peak difference in the concentration of CO2 in inhaled andexhaled air of the patient, the clinician programmer determines theefficiency of each inspiration phase in the respiratory cycle based onthe measured physiological parameter, and computes the score based onthe determined efficiency of each inspiration phase in the respiratorycycle.

In still another embodiment, the feedback mechanism comprises one ormore electro-myographic (EMG) sensors, the measured physiologicalparameter is an electrical potential generated by the muscle cells of atongue of the patient, and the clinician programmer determines theextent to which one or more tongue protusor muscles are activated basedon the measured physiological parameter, and computes the score based onthe determined extent to which the one or more tongue protrusor musclesare activated.

In yet another embodiment, the feedback mechanism comprises one or morecameras, the physiological parameter is a picture of the airway of thepatient, clinician programmer determines the extent to which the airwayof the patient is obstructed based on the measured physiologicalparameter, and computes the score based on the determined extent towhich the airway of the patient is obstructed.

In still yet another embodiment, the feedback mechanism comprises one ormore inertial sensors, the measured physiological parameter comprises isthe movement of the tongue of the patient, the clinician programmerdetermines the extent to which the tongue of the patient protrudes basedon the measured physiological parameter, and computes the score based onthe determined extent to which the tongue of the patient protrudes.

In accordance with a sixth aspect of the present inventions, a method oftitrating (or equivalently, “fitting”) a neurostimulation system thattreats obstructive sleep apnea (OSA) comprises circumferentiallydisposing a plurality of electrode contacts around a trunk of ahypoglossal nerve (HGN) (e.g., on the HGN trunk proximal to a medialbranch of the HGN trunk). In one method, the nerve has a diameter in therange of 2.5 mm to 4.0 mm. In another method, the electrode contactscircumferentially span at least a 180-degree arc around nerve. In stillanother method, the electrode contacts circumferentially span at least a270-degree arc around the nerve. In yet another method, acenter-to-center spacing of each pair of adjacent ones of electrodecontacts is equal to or less than twice the width of each electrodecontact of the respective pair of electrode contacts.

The method further comprises sequentially delivering an electrical pulsetrain to each of a plurality of sets of the electrode contacts. As oneexample, each set of electrode contacts may comprise a pair of adjacentones of the electrode contacts, in which case, the electrical pulsetrain may be sequentially delivered to each set of electrode contacts ina bipolar mode. As another example, each set of electrode contacts maycomprise a single electrode contact and the neurostimulator (or IPG)housing the indifferent or return electrode, in which case, theelectrical pulse may be sequentially delivered to each electrode contactor set of contacts in a monopolar mode. And in some cases, non-adjacentelectrode contact pairs or even more than two non-adjacent contacts maybe chosen for either bipolar or monopolar stimulation.

In one exemplary method, the electrical pulse train has an initial,preconditioning current or voltage amplitude and a subsequent higherstimulating current or voltage amplitude, such that one or moreperipherally located nerve fascicles in the nerve are pre-conditioned bythe initial preconditioning current or voltage amplitude, and one ormore centrally located nerve fascicles in the nerve further away fromthe at least one electrode than the peripherally located nerve fasciclesare triggered by the higher stimulating current or voltage amplitude,while the one or more pre-conditioned peripherally located nervefascicles are not triggered by the higher stimulating current or voltageamplitude.

The method further comprises measuring a physiological parameter of thepatient indicative of an efficacy of the delivered electrical pulsetrain in treating the OSA. As examples, the physiological parameter maycomprise one or more of measuring the temperature of inhaled and exhaledair of a patient, measuring a concentration of CO2 in inhaled andexhaled air of the patient, measuring the electrical potential generatedby the muscle cells of a tongue of the patient, capturing pictures ofthe airway of the patient, and measuring the movement of the tongue ofthe patient.

The method further comprises selecting one of the sets of electrodecontacts based on the measured physiological parameter. In one method,the electrical pulse train is delivered from a neurostimulator, in whichcase, the method may further comprise programming the neurostimulatorwith the selected set of electrode contacts. The method may furthercomprise computing a score of each of the electrode contact sets basedon the respective measured physiological parameter. One method furthercomprises determining the efficiency of each inspiration phase in therespiratory cycle based on the measured physiological parameter, andcomputing the score based on the determined efficiency of eachinspiration phase in the respiratory cycle

The measured physiological parameter may comprise a peak-to-peakdifference in temperature of inhaled and exhaled air of the patient, andthe method may further comprise determining the efficiency of eachinspiration phase in the respiratory cycle based on the measuredpeak-to-peak difference in temperature of inhaled and exhaled air of thepatient, in which case, the score may be computed based on thedetermined efficiency of each inspiration phase in the respiratorycycle.

The measured physiological parameter may comprise a peak-to-peakdifference in the concentration of CO2 in inhaled and exhaled air of thepatient, and the method further comprises determining the efficiency ofeach inspiration phase in the respiratory cycle based on the measuredpeak-to-peak difference in the concentration of CO2 in inhaled andexhaled air of the patient, in which case, the score may be computedbased on the determined efficiency of each inspiration phase in therespiratory cycle.

The measured physiological parameter may comprise an electricalpotential generated by the muscle cells of a tongue of the patient, themethod further comprising determining the extent to which one or moretongue protusor muscles are activated based on the measured electricalpotential generated by the muscle cells of a tongue of the patient, inwhich case, the score may be computed based on the determined extent towhich the one or more tongue protrusor muscles are activated.

The measured physiological parameter may comprise a picture of theairway of the patient, and the method may further comprises determiningthe extent to which the airway of the patient is obstructed based on thepicture of the airway of the patient, in which case, the score may becomputed based on the determined extent to which the airway of thepatient is obstructed.

The measured physiological parameter may comprise a movement of thetongue of the patient, and the method may further comprise determiningthe extent to which the tongue of the patient protrudes based on themovement of the tongue of the patient, in which case, the score may becomputed based on the determined extent to which the tongue of thepatient protrudes.

In accordance with a seventh aspect of the present inventions, animplantable neurostimulator for use in a patient having obstructivesleep apnea comprises a case and stimulation circuitry contained withinthe case. The stimulation circuitry is configured for generating anelectrical pulse train. In one embodiment, the electrical pulse trainhas an initial, preconditioning current or voltage amplitude and asubsequent higher stimulating current or voltage amplitude. Theneurostimulator further comprises sensing circuitry comprising a sensor(e.g., at least one of a pressure sensor and an inertial sensor) affixeddirectly to or within the case. The sensor is configured for sensingphysiological artifacts that are caused by respiration.

The neurostimulator further comprises control circuitry contained withinthe case. The control circuitry configured for causing the stimulationcircuitry to deliver the electrical pulse train to at least oneelectrode contact in synchronization with a respiratory cycle based onthe sensed physiological artifacts. In one embodiment, the controlcircuitry is configured for determining the next projected onset of aninspiratory phase of the respiratory cycle based on the sensedphysiological artifacts, and causing the stimulation circuitry todeliver the electrical pulse train to the electrode contact(s)immediately before, at, or right after the next projected onset of theinspiratory phase of the respiratory cycle.

In one embodiment, the neurostimulator further comprises a receptacleconfigured for receiving at least one proximal contact of an electrodelead that carries the electrode contact(s). In another embodiment, theneurostimulator further comprises memory configured for storing datarepresentative of the physiological artifacts sensed by the e sensor(s).The neurostimulator may optionally comprise a motion detector affixeddirectly to or within the case. The sensor(s) may comprise the motiondetector. The motion detector may be configured for sensing a tap on theneurostimulator, and the control circuitry may be configured fortoggling the neurostimulator between an ON position and an OFF positionin response at least one tap, such that in the OFF position, nostimulation energy is delivered to the at least one electrode contact.As one example, the control circuitry may be configured for toggling theneurostimulator between an ON position and an OFF position in responseto a plurality of successive taps (e.g., less than one second apart).

A neurostimulation system may comprise an electrode lead carrying theelectrode contact(s), and the neurostimulator, with the receptacle beingconfigured for receiving the electrode lead. The electrode lead maycarry a plurality of electrode contacts, in which case, theneurostimulation system may further comprise a clinician programmerconfigured for selecting the electrode contact(s) from the electrodecontacts, transcutaneously communicating with the neurostimulator, andprogramming the control circuitry to deliver the electrical pulse trainto the selected electrode contact(s). The neurostimulation system mayfurther comprise a patient programmer configured for transcutaneouslycommunicating with the neurostimulator, and toggling the neurostimulatorbetween the OFF position and the ON position. The neurostimulator mayfurther comprise a rechargeable battery contained within the case, inwhich case, the neurostimulation system may further comprise an externalcharger configured for inductively and transcutaneously charging therechargeable battery of the neurostimulator.

In accordance with an eighth aspect of the present inventions, animplantable neurostimulator for use in a patient having an ailmentcomprises a case and stimulation circuitry contained within the case.The stimulation circuitry is configured for generating an electricalpulse train. In one embodiment, the electrical pulse train has aninitial, preconditioning current or voltage amplitude and a subsequenthigher stimulating current or voltage amplitude.

The neurostimulator further comprises control circuitry contained withinthe case. The control circuitry is configured for causing thestimulation circuitry to deliver the electrical pulse train to at leastone electrode contact. The neurostimulator may further comprise areceptacle configured for receiving at least one proximal contact of anelectrode lead that carries the electrode contact(s).

The neurostimulator further comprises a motion detector (e.g., one of apressure sensor and an inertial sensor) affixed directly to or withinthe case, the motion detector configured for sensing a tap on theneurostimulator, wherein the control circuitry is configured fortoggling the neurostimulator between an ON position and an OFF positionin response to a plurality of successive taps, such that in the OFFposition, no stimulation energy is delivered to the at least oneelectrode contact. In one embodiment, the control circuitry isconfigured for toggling the neurostimulator between an ON position andan OFF position in response to a plurality of successive taps less thanone second apart.

In another embodiment, the neurostimulator further comprises sensingcircuitry comprising at least one sensor affixed directly to or withinthe case. The sensor(s) may comprise the motion detector. The sensor(s)is configured for sensing physiological artifacts that are caused byrespiration, and the control circuitry is configured for causing thestimulation circuitry to deliver the electrical pulse train insynchronization with a respiratory cycle based on the sensedphysiological artifacts. In this case, the control circuitry may beconfigured for determining the next projected onset of an inspiratoryphase of the respiratory cycle based on the sensed physiologicalartifacts, and causing the stimulation circuitry to deliver theelectrical pulse train to the electrode contact(s) immediately before,at, or right after the next projected onset of the inspiratory phase ofthe respiratory cycle. The neurostimulator may further comprise memoryconfigured for storing data representative of the physiologicalartifacts sensed by the sensor(s).

A neurostimulation system may comprise an electrode lead carrying theelectrode contact(s), and the neurostimulator, with the receptacle beingconfigured for receiving the electrode lead. The electrode lead maycarry a plurality of electrode contacts, in which case, theneurostimulation system may further comprise a clinician programmerconfigured for selecting the electrode contact(s) from the electrodecontacts, transcutaneously communicating with the neurostimulator, andprogramming the control circuitry to deliver the electrical pulse trainto the selected electrode contact(s). The neurostimulation system mayfurther comprise a patient programmer configured for transcutaneouslycommunicating with the neurostimulator, and toggling the neurostimulatorbetween the OFF position and the ON position. The neurostimulator mayfurther comprises a rechargeable battery contained within the case, inwhich case, the neurostimulation system may further comprise an externalcharger configured for inductively and transcutaneously charging therechargeable battery of the neurostimulator.

In accordance with a ninth aspect of the present inventions, animplantable neurostimulator is provided for use in a patient having anailment comprises a case and stimulation circuitry contained within thecase. The stimulation circuitry is configured for generating anelectrical pulse train. In one embodiment, the electrical pulse trainhas an initial, preconditioning current or voltage amplitude and asubsequent higher stimulating current or voltage amplitude.

The neurostimulator further comprises sensing circuitry comprising atleast one sensor (e.g., one of a pressure sensor and an inertial sensor)affixed directly to or within the case. The sensor(s) is configured forsensing a physiological parameter of patient and sensing a tap on theneurostimulator.

The neurostimulator further comprise control circuitry contained withinthe case. The control circuitry is configured for causing thestimulation circuitry to deliver the electrical pulse train to at leastone electrode contact based on the sensed physiological parameter, andfor toggling the neurostimulator between an ON position and an OFFposition in response at least one tap, such that in the OFF position, nostimulation energy is delivered to the electrode contact(s). As oneexample, the control circuitry may be configured for toggling theneurostimulator between an ON position and an OFF position in responseto a plurality of successive taps (e.g., less than one second apart). Inone embodiment, the neurostimulator further comprises a receptacleconfigured for receiving at least one proximal contact of an electrodelead that carries the electrode contact(s).

Other and further aspects and features of the invention will be evidentfrom reading the following detailed description of the preferredembodiments, which are intended to illustrate, not limit, the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

The drawings illustrate the design and utility of preferred embodimentsof the present invention, in which similar elements are referred to bycommon reference numerals. In order to better appreciate how theabove-recited and other advantages and objects of the present inventionsare obtained, a more particular description of the present inventionsbriefly described above will be rendered by reference to specificembodiments thereof, which are illustrated in the accompanying drawings.

Understanding that these drawings depict only typical embodiments of theinvention and are not therefore to be considered limiting of its scope,the invention will be described and explained with additionalspecificity and detail through the use of the accompanying drawings inwhich:

FIG. 1 is a cut-away anatomical drawing of the head and neck areaillustrating the muscles that control movement of the tongue and thehypoglossal nerve and its branches that innervate these muscles;

FIG. 2 is a plan view of a stimulation system constructed in accordancewith one embodiment of the present inventions;

FIG. 3 is a block diagram of the internal components of an implantablepulse generator of the stimulation system of FIG. 2;

FIG. 4 is a perspective view of a lead electrode that may be used in thestimulation system of FIG. 2;

FIG. 5 is a plan view of a nerve cuff electrode of the lead electrode ofFIG. 4, particularly shown in an unfurled state;

FIG. 6 is a cross-sectional view of the nerve cuff electrode of FIG. 5,particularly shown in a furled state;

FIG. 7a is a diagram of an electrical pulse train that can be generatedby the stimulation system of FIG. 2;

FIG. 7b is a diagram of a bi-phasic, charge-balanced, symmetricalelectrical pulse train that can be generated by the stimulation systemof FIG. 2;

FIG. 7c is a diagram of a bi-phasic, charge-balanced, asymmetricalelectrical pulse train that can be generated by the stimulation systemof FIG. 2;

FIG. 7d is a diagram of a bi-phasic, asymmetrical electrical pulse trainhaving a quiescent period that can be generated by the stimulationsystem of FIG. 2;

FIG. 8 is a diagram of a pre-conditioning electrical pulse train thatcan be generated by the stimulation system of FIG. 2;

FIG. 9 is a flow diagram illustrating one method of implanting andfitting the stimulation system of FIG. 2 to a patient.

FIG. 10 is a plan view of a stimulation system constructed in accordancewith another embodiment of the present inventions;

FIG. 11 is a diagram of an exemplary temperature change measurementtaken by a feedback mechanism of the stimulation system of FIG. 10 froma breath during respiration of a patient;

FIG. 12 is a diagram of an exemplary CO2 concentration measurement takenby a feedback mechanism of the stimulation system of FIG. 10 from abreath during respiration of a patient; and

FIG. 13 is a flow diagram illustrating one method of titrating orfitting the stimulation system of FIG. 10 to a patient.

DETAILED DESCRIPTION

Referring first to FIG. 1, it is desirable to locate a nerve cuffelectrode 10 around a trunk 14 of a hypoglossal nerve (HGN) 12 forpurposes of stimulating the muscles that move the tongue 16 forward, andin particular, the fascicles of the HGN 12 that innervate the tongueprotrusor muscles, such as the genioglossus 18 and/or the geniohyoidmuscles 20, thereby preventing or alleviating obstructive apneic events.As shown, the nerve cuff electrode 10 is positioned on the HGN trunk 14immediately before it branches out, and hence at a proximal position 22to the HGN branches 24. In the illustrated embodiment, the proximalposition 22 is just prior to the medial branch of the HGN 12 thatinnervates the tongue protrusor muscles.

As briefly discussed above, the implantation of the nerve cuff electrode10 at this proximal position 22 reduces the surgical time and effort,allows more surgeons to perform the surgery, reduces the risk and traumato the patient, and reduces engineering design complexity and cost.However, it introduces the problem of inadvertently stimulating otherfascicles of the HGN trunk 14 that innervate muscles in opposition tothe tongue protrusor muscles, i.e., the tongue retractor muscles, e.g.,the hyoglossus 26 and styloglossus muscles 28, as well as the intrinsicmuscles of the tongue 16.

As also briefly discussed above, it is further desirable to synchronizethe stimulation of the HGN 12 with the respiratory cycle of the patient,so that tongue 16 is anteriorly moved in response to the stimulation ofthe HGN 12 when it is most needed, and in particular, right before theonset of the next inspiratory phase of the respiratory cycle. Suchsynchronization requires detection or prediction of the onset of theinspiratory phase using one or more sensors. The conventional thought isthat the sensor(s) should be implanted within anatomical structures,such as the ribcage and abdomen, the movement of which stronglycorrelates to the respiratory cycle of the patient. However, because theneurostimulator will typically be implanted in the upper chest portionof the patient away from these anatomical structures, one or more leadsmust be used to implant the sensor(s) within these anatomical structuresremote from the neurostimulator, thereby requiring additional surgicaltime and effort.

Systems and methods are described herein that selectively stimulate thefascicles of the HGN 12 at the proximal position 22 of the HGN 12 thatinnervate the genioglossus 18 and/or the geniohyoid muscles 20, whilesynchronizing the stimulation with the respiratory cycle of the patientwithout the need to implant sensor(s) remotely from the neurostimulator.

Referring to FIG. 2, one embodiment of a stimulation system 50 thatselectively stimulates the fascicles of the trunk 14 of the HGN 12 thatinnervate the tongue protrusor muscles for treating obstructive sleepapnea (OSA) will now be described. The system 50 generally comprises animplantable device 52, an electrode lead 54, an external charger 55, aclinician programmer 56, and a patient programmer 58. The electrode lead54 and the implantable device 52, or alternatively, an implantable pulsegenerator (“IPG”) or a “neurostimulator,” can be implanted within apatient. In this patent disclosure we will use terms “IPG” and“neurostimulator”, equivalently.

The electrode lead 54 comprises the aforementioned nerve cuff electrode10 and a lead body 60 coupling the nerve cuff electrode 10 to theimplantable device 52 via a proximal lead connector 62 and acorresponding connector receptacle 64. Although the lead body 60 can bestraight, in the illustrated embodiment, the lead body 60 may have oneor more S-shaped sections in order to provide strain relief, therebyaccommodating body movement at the location where the lead body 60 isimplanted. This strain relief feature is advantageous, since the leadbody 60 is intended to be implanted in a body location such as the neck,where the lead body 60 is subjected to frequent movement and stretching.Thus, the S-shape of the lead body 60 can help prevent damage to the HGNtrunk 14, resulting from sometimes, unavoidable pulling of the nervecuff electrode 10 as a result of neck movements. As will be described infurther detail, the nerve cuff electrode 10 comprises an array ofcircumferentially disposed electrode contacts.

Although only a single electrode lead 54 is shown in FIG. 2, someembodiments of the present system may have an IPG 52 having tworeceptacles 64 (not shown) for attaching two electrode leads, eachelectrode lead having a nerve cuff electrode 10. In such a two-electrodelead system, each nerve cuff electrode 10 can be implanted bilaterallyto each of the HGN trunks 14. However, it has been determined that onlya single nerve cuff electrode 10 implanted at the HGN trunk 14 on eitherside (unilaterally) can provide sufficiently effective stimulation toprotrude the tongue to control OSA. A unilateral stimulation system isadvantageous, since it is simpler in numbers of components used andrequires only half the surgery to implant only a single nerve cuffelectrode 10, instead of two.

The IPG 52 comprises an outer case 66 for housing the electronic andother components (described in further detail below). In one embodiment,the outer case 66 may comprise an electrically conductive, biocompatiblematerial, such as titanium or titanium alloy, and form a hermeticallysealed compartment wherein the internal electronics are protected fromthe body tissue and fluids. In some cases, the outer case 66 may serveas an electrode. As briefly discussed above, the IPG 52 furthercomprises a receptacle 64 to which the proximal end of the lead body 60mates in a manner that electrically couples the nerve cuff electrode 10to the internal electronics (described in further detail below) withinthe outer case 66.

Referring now to FIG. 3, the components and circuitry housed in theouter case 66 comprise stimulation circuitry 68, control circuitry 70,communication circuitry 72, memory 74, sensing circuitry 76, arechargeable power source 77, and power circuitry 79, which all may beconveniently mounted on a printed circuit board (PCB) (not shown).

In one embodiment, the sensing circuitry 76 comprises one or moresensor(s) (not shown) that are contained in the outer case 66 orotherwise attached as an integral part of the IPG 52, such as affixed tothe exterior of the outer case 66. Further details on incorporation ofsensors within or on the outer case of an IPG 52 are described in U.S.patent application Ser. No. 15/374,538, entitled “Implantable PressureSensors and Medical Devices,” which is expressly incorporated herein byreference. In other alternative embodiments, the sensor(s) can bepositioned at a site remote from the IPG 52 coupled by a connectinglead, e.g., as described in U.S. patent application Ser. No. 15/093,495,entitled “Upper Airway Stimulator Systems for Obstructive Sleep Apnea,”which is expressly incorporated herein by reference, although as can beappreciated, this would require additional surgery and time to implantthe sensing lead.

The sensing circuitry 76 is used primarily to sense the respirationcycle and can, in embodiments of the invention, determine a projectedonset of the inspiratory phase of the breathing cycle, or alternatively,may determine the projected onset of the expiratory phase of thebreathing cycle. In particular, the sensing circuitry 76 is configuredfor detecting physiological artifacts that are caused by respiration(e.g., movement or expansion of ribcage and/or abdomen), which areproxies for respiratory phases, such as inspiration and expiration or,if no movement occurs, to indicate when breathing stops. For example,the sensing circuitry 76 may sense movement of the thoracic cavityand/or detect changes in pressure/force in the thoracic cavity. Thus,the sensing circuitry 76 is configured for acquiring, conditioning, andprocessing signals related to respiration. The sensor(s) of the sensingcircuitry 76 can take the form of, e.g., inertial sensors (e.g.,accelerometers or gyroscopes), pressure sensors, bioimpedance sensors,ECG electrodes, temperature sensors, GPS sensors, or some combinationthereof.

The stimulation circuitry 68 is coupled to the nerve cuff electrode 10via the lead body 60, and is configured for delivering stimulation tothe HGN trunk 14 via selected ones of the electrode contacts 82. Thecontrol circuitry 70 is coupled to the stimulation circuitry 68 andcontrols when, and for how long, the stimulation circuitry 68 appliesstimulation to the HGN trunk 14. The control circuitry 70 may alsocontrol the intensity of the stimulation applied by the stimulationcircuitry 68 to the HGN trunk 14, e.g., by varying the amplitude, pulsewidth, or frequency of the stimulation.

As will be described in further detail below, the control circuitry 70may select the optimal electrode contact(s) of the nerve cuff electrode10 used for stimulating the HGN trunk 14, and in particular, theelectrode contact(s) that stimulate the fascicles of the HGN 12innervating the tongue protrusor muscles, e.g., the genioglossus 18 orgeniohyoid 20 muscles, to thereby prevent or alleviate obstructiveapneic events. However, stimulation of nerve fascicles innervating thetongue retractor muscles, e.g., the hyoglossus 26 and styloglossusmuscles 28, as well as the intrinsic muscles of the tongue 16, should beavoided to the extent possible.

The memory 74 is configured for storing specific data gathered by thesensing circuitry 76 and programming instructions and stimulationparameters. The control circuitry 70 may recall the sensed data from thememory 74 and analyze it to determine when stimulation should bedelivered to the HGN trunk 14 to synchronize the stimulation deliverywith the respiratory cycle. In some embodiments, the sensor data may beanalyzed to predict the onset of the next inspiratory phase of thebreathing cycle and to deliver stimulation right before, at, or slightlyafter the predicted onset of the inspiratory phase.

Thus, when the patient is in the inspiratory portion of the respiratorycycle—where the patient is breathing in or attempting to breath in, thecontrol circuitry 70 may, in some embodiments, apply stimulation,thereby causing forward displacement of the tongue, and causing theupper airway to remain un-obstructed during inspiration while sleeping.The control circuitry 70 causes the stimulation circuitry 68 to applystimulation during these inspiratory phases of the respiratory cycle (orapplying stimulation starting slightly before the inspiration and endingat the end of inspiration), and not the remainder of the respirationcycle, when all other conditions for stimulation are met.

The IPG 52 may be toggled between an ON position and an OFF positionusing one of a variety of techniques. In one embodiment, the IPG 52 mayhave a magnetic reed switch (not shown) contained within the outer case66 that can sense a magnetic field from an external magnet. An externalmagnet may be used to toggle the IPG 52 to the OFF position oralternatively to an ON position. Oftentimes, patients may need toundergo an MRI scan. A reed switch in the IPG 52 may make it MRIincompatible. In another embodiment, the IPG 52 may have a sensor (notshown) that is sensitive to movement (i.e., a motion detector), such asan inertial sensor (e.g., an accelerometer or gyroscope), and a switchthat can be toggled between a closed state and an open state to placethe implanted IPG 52 between an ON position and an OFF position bytapping the implanted IPG 52 with the hand. For example, one tap mayswitch the IPG 52 from an ON position to an OFF position, and anothertap may switch the IPG 52 from an OFF position to an ON position. In onepreferred embodiment, the same sensing circuitry 76, along with thesensor, that is used for detecting physiological artifacts that arecaused by respiration, may be used to sense the tapping of the implantedIPG 52 to toggle the IPG 52 between the ON position and the OFFposition.

In another preferred embodiment, the IPG 52 can be toggled between an ONposition and an OFF position in response to multiple quick successivetaps (e.g., less than a second between taps), as opposed to a singletap, which may occur by accidental bumping and cause an inadvertent turnoff of the IPG; for example, two taps to switch the IPG 52 from an ONposition to an OFF position, and two taps to switch the IPG 52 from anOFF position to an ON position. As a redundancy, the patient programmer58 or the clinician programmer 56 may also be configured to be able totoggle the IPG 52 from ON to OFF and from OFF to ON.

In an optional embodiment, the sensing circuitry 76 comprises a bodyposition sensor (not shown) (e.g., an inertial sensor) configured formeasuring an orientation of the patient's body. In this case, thecontrol circuitry 70 determines the orientation of the patient's body,and activates the portions of the sensing circuitry 76 that monitor thephysiological artifacts that are caused by respiration when theorientation indicates that the patient is in an apneic position (i.e., aposition in which the patient is likely to experience apneic events).The most common apneic position is supine, but can include left side,right side, or both. Patients with positional sleep apnea experiencesignificantly more apneic events while in particular apneic positions,thereby allowing the neurostimulator 52 to preserve battery life bymonitoring the physiological artifacts that are caused by respirationonly when the patient is likely to experience apneic events. The memory74 may store positional sleep apnea data for the patient that can beconsulted by the control circuitry 70 when determining whether thepatient is in an apneic position.

In another optional embodiment, the sensing circuitry 76 comprises asleep sensor (not shown) configured for measuring a physiologicalparameter indicative of whether the patient is sleeping. The sleepsensor may comprise sensors used in polysomnography, such as an EMGsensor across the jaw line, an EEG sensor, and an EOG sensor, aninertial sensor, or a temperature sensor. In this case, the controlcircuitry 70 determines whether the patient is asleep, and activates theportions of the sensing circuitry 76 that monitor the physiologicalartifacts that are caused by respiration only when the patient isasleep. This preserves battery life since sensing and monitoring onlyoccurs when the patient is actually asleep.

Further details describing the use of body orientation and sleep sensorsare discussed in U.S. patent application Ser. No. 15/093,627, entitled“Upper Airway Stimulator Systems for Obstructive Sleep Apnea,” which isexpressly incorporated herein by reference.

The communication circuitry 72 is configured for wirelesslycommunicating transcutaneously (through the patient's skin) with theclinician programmer 56 and patient programmer 58 using radio frequency(RF) signals, e.g., via an Off The Shelf (OTS) Inductive/Bluetooth/MICSradio link. The communication circuitry 72 may include one or more ACcoils for transmitting and receiving the RF signals to and from theclinician programmer 56 and patient programmer 58.

The rechargeable power source 77, for example, a rechargeable battery,and power circuitry 79 are configured for providing operating power tothe IPG 52. The rechargeable power source 77 may comprise a lithium-ionor lithium-ion polymer battery, and provide an unregulated voltage tothe power circuitry 79. The power circuitry 79, in turn, generatesregulated or unregulated voltage to the various circuits located withinthe IPG 52. The rechargeable power source 77 is recharged usingrectified AC power received by an AC receiving coil (such as one of thecoils coupled to the communication circuitry 72) from the externalcharger 55. The AC magnetic field emitted by the external charger 55induces AC currents in the AC receiving coil (not shown), which isrectified by circuitry (not shown) that rectifies the AC current toproduce DC current that is used to charge the power source 77.

Referring back to FIG. 2, to recharge the IPG 52, the external charger55 or a part of the charger having a coil, which generates the ACmagnetic field, is placed against, or otherwise adjacent, to thepatient's skin over the implanted IPG 52. The clinician programmer 56may be used to transcutaneously communicate with the implanted IPG 52for programming the IPG 52 and querying the IPG 52 for status. Forexample, the clinician programmer 56 can be used to configure certainprograms and processes used by the control circuitry 70 in the IPG 52 todetermine when the stimulation pulses are to be delivered to electrodecontacts of the nerve cuff electrode 10. The clinician programmer 56 canalso be used to program specific stimulus parameters, such as stimuluspulse width, stimulus frequency, duration of a train pulses and pulseamplitude. The amplitude may be expressed in current, for example,milliamperes, or it could be expressed in volts, such as 0.3 volts. Thechoice between milliamperes or volts to express stimulus amplitude willdepend on whether the design of the stimulation circuitry 68 providesstimulus pulses that are constant voltage or constant current. Anotherimportant function of the clinician programmer 56 is the ability toselect modes of stimulation. For example, the IPG 52 may operate in amonopolar stimulation mode (also sometimes referred to as a “unipolar”mode) and in a bipolar stimulation mode.

As used in this present disclosure, a monopolar stimulation mode meansthat one of the electrode contacts used is at least a portion of theouter case 66 that will function as an indifferent/anode electrode. Theindifferent electrode is part of the electrical circuit with at leastone electrode contact of the nerve cuff electrode 10 as theactive/cathode electrode contact that stimulates the HGN trunk 14.Generally, that part of the outer case 66 that is acting as theindifferent electrode does not stimulate any tissue or nerve, but merelyfunctions as a return electrode and may be a biocompatible, conductivemetal such as a titanium alloy, as discussed above.

A bipolar stimulation mode means, for purposes of this disclosure, thatthe outer case 66 is not part of the stimulation circuit. At least twoelectrode contacts of the nerve cuff electrode 10 must be selected andwill be part of the bipolar mode electrical stimulation circuit.Sometimes a stimulation circuit can have three or even more electrodecontacts functioning together. This may also be referred to as “bipolar”stimulation mode even though there are sometimes more than two activeelectrode contacts in the stimulation circuit. Sometimes athree-electrode contact system may be referred to as a tripolar circuit.For purposes of this disclosure and application, we will consider athree or more electrode-contact stimulation circuit (if it excludes theouter case 66) as variants of a bipolar stimulation mode and will beincluded as within a “bipolar” stimulation mode. The present stimulationsystem in its various embodiments, thus, may operate in either monopoloror bipolar stimulation modes.

Significantly, to facilitate selective stimulation of the fascicles ofthe HGN 12 that innervate the tongue protrusor muscles, the clinicianprogrammer 56 also selects which electrode contacts of the nerve cuffelectrode 10 or the indifferent electrode of the outer case 66 are to bein the stimulation circuit. The clinician programmer 56 may also be ableto query the status of the IPG 52 for a number of status functions, suchas battery status. Another query may be whether the IPG 52 is in an ONposition or an OFF position. In the ON position, the stimulationcircuitry 68 within the IPG 52 is enabled and stimulation pulses can bedelivered via the selected electrode contact or contacts of the nervecuff electrode 10. When the patient is awake, the IPG may be placedautomatically or by choice into the OFF position or mode, and thestimulation circuitry 68 is not enabled and no stimulation can occur.

The patient programmer 58 offers more limited programming options thanthe clinician programmer 56. The patient programmer 58 may provide theoption to toggle the IPG 52 into the OFF position or into the ONposition. Also, the stimulus pulse amplitudes may be adjusted for alimited range of up and down. Often the patient programmer 58, becauseof limited functionality, may be in a package or form that is muchsmaller in size than the clinician programmer 56. The clinicianprogrammer 56 and patient programmer 58 may take the form of commercialelectronic smart devices on which there are installed customizedapplications for performing the afore-described functions.

Referring now to FIGS. 4-6, an embodiment of an electrode lead 54 thatmay be used in the stimulation system will now be described in furtherdetail. The proximal lead connector 62 comprises a linear array ofconnector contacts 78 a-78 f (in this case, six) for connecting to theconnector receptacle 64 of the IPG 52 when the proximal lead connector62 is inserted into the connector receptacle 64.

The nerve cuff electrode 10 further comprises a nerve cuff body 80 thatis capable of substantially or completely encircling the HGN trunk 14.The nerve cuff electrode 10 may be, in some embodiments, manufactured tobe self-curling, and may be designed to self-adjust in accordance withthe diameter of the HGN trunk 14. The material used for the electrodesubstrate can be typical implantable electrode materials, such assilicone, polyurethane or other less conventional implant materials,e.g., liquid crystal polymers. The material consistency of the formedcuff body 80 should be pliable enough to allow the clinician to unfoldthe cuff, as shown in FIG. 5, and placed around the HGN trunk 14 and tohave the nerve cuff electrode 10 curl back around itself, as shown inFIG. 6. Although FIG. 5 illustrates the lead body 60 in the middle ofthe cuff body 80, the lead body 60 can be positioned at either the leftor right end of the cuff body 80, and the lead body 60 may even point 90degrees from the direction the lead body 80 is aligned as shown in FIG.5. The substrate material of the nerve cuff body 80, therefore, shouldhave a memory property to the extent that it will tend to return to itsoriginal curled shape. In one advantageous manufacturing process, thenerve cuff electrode 10, lead body 60, and proximal lead connector 62may be constructed of a flexible circuit, as described in U.S. patentapplication Ser. Nos. 15/634,057 and 15/634,134, both entitled “NerveCuff Electrodes Fabricated Using Over-Molded LCP Substrates,” which areexpressly incorporated by reference.

The nerve cuff electrode 10, as shown, will also have some give, so thatif the nerve swells during the inflammatory phase post-surgery, theinner lumen size of the nerve cuff electrode 10 can expand andaccommodate to the nerve swelling. This capability of self-adjustmentover time is important because once tissue has been dissected fromaround the nerve, there often will be an inflammatory response aroundthe damaged tissue and also in response to the presence of foreignmatter that may be introduced during the surgical implantation of thenerve cuff electrode 10. Indeed, the nerve cuff electrode 10, itself, islikely seen as a foreign matter contributing to inflammation. Theinflammatory response may be ongoing over a period of months. Duringthis period, the nerve, itself, may swell up and increase substantiallyin diameter, perhaps up to 50% more than before the surgery. Once pastthis inflammatory response, the nerve diameter may then decrease insize, closer to its original diameter. If the inner lumen size of thenerve cuff electrode 10 does not adjust in size to accommodate theincrease in the nerve diameter, constriction of the target nerve canresult in traumatic cell damage and nerve death. Further detailsdescribing various self-expanding nerve cuff electrodes are set forth inU.S. Provisional Patent Application Ser. No. 62/500,080, entitled “NerveCuff Electrode Locking Mechanism,” and U.S. Provisional PatentApplication Ser. No. 62/500,091, entitled “Self-Expanding Nerve CuffElectrode,” which are both expressly incorporated herein by reference.

The nerve cuff electrode 10 further comprises an array of electrodecontacts 82 a-82 f (in this case, six) affixed to an inner surface ofthe cuff body 80 (when furled), such that when the cuff body 80encircles the HGN trunk 14, the electrode contacts 82 a-82 f are incontact with the HGN trunk 14. To facilitate selective activation of thefascicles of the HGN trunk 14 that innervate the protrusor muscles, theelectrode contacts 82 are affixed to the cuff body 80 in a manner, suchthat when the cuff body 80 encircles the HGN trunk 14, the electrodecontacts 82 are circumferentially disposed about the HGN trunk 14. Inthis case, the electrode contacts 82 span the cuff body 80circumferentially around the HGN trunk 14. The electrode contacts 82a-82 f preferably circumferentially span at least a 180-degree arc ofthe HGN trunk 14, and more preferably span at least a 270-degree arc ofthe HGN trunk 14, so that any fascicle within the HGN trunk 14 can beselectively stimulated by delivering stimulation energy from theelectrode contact or contacts 82 adjacent to the fascicle, as describedin further detail below. To facilitate coverage of all of the fascicles,the number of electrode contacts 82 preferably equals at least three,and more preferably, at least six. The electrode contacts 82 are alsoaligned on the inner surface of the cuff body 80, such that, when thecuff body 80 encircles the HGN trunk 14, the electrode contacts 82 areaxially aligned with each other. For the purposes of this specification,electrode contacts 82 are axially aligned with each other if they lie inthe same plane that is perpendicular to the axis of the cuff body 80 oraxis of the HGN trunk 14. In addition, although FIG. 5 shows anembodiment of cuff having electrode contacts aligned in a single row, inother embodiments, it is possible to construct a cuff having two or evenmore parallel rows of electrode contacts (not shown) that are parallelto the direction defined by electrode contacts 82 a-82 f. The latterelectrode contact arrangement(s) will provide an additional degree offreedom in stimulating a target nerve fascicle.

Although the exemplary nerve cuff electrode 10 comprises six electrodecontacts 82 a-82 f, other nerve cuff electrodes may have two to fiveelectrode contacts 82 or more than six electrode contacts 82. Thepreferred range, however, of the numbers of electrode contacts 82 on anyparticular nerve cuff electrode is between three to eight electrodecontacts 82, so as to surround the circumference of the HGN trunk 14,and provide a sufficient number of independent electrode channels fromwhich to select and to recruit the protrusor muscles without recruitingthe retractor muscles. The connector contacts 82 a-82 f are respectivelyand independently electrically coupled to the electrode contacts 82 a-82f via electrical conductors (not shown), such that the electrodecontacts 82 a-82 f may be independently activated in either monopolarstimulation mode or bipolar stimulation mode. In the monopolarstimulation mode, one or more of the electrode contacts 82 a-82 f willpreferably be activated as cathode(s), whereas in the bipolarstimulation mode, one or more of the electrode contacts 82 a-82 f willbe activated as cathode(s), and one or more other electrode contacts 82a-82 f will be activated as anode(s).

Although in some embodiments, the nerve cuff electrode 10 may beoperated in a monopolar stimulation mode, requiring that only oneelectrode contact 82 of the nerve cuff electrode 10 be activated at anygiven time, as will be described in further detail below, it isdesirable that the nerve cuff electrode 10 be operated in a bipolarstimulation mode to facilitate selective recruitment of the fascicles 15in the HGN trunk 14, requiring that at least two electrode contacts 82of the nerve cuff electrode 10 be activated at any given time.

That is, monopolar stimulation results in a more diffuse electricalfield that will tend to recruit most fascicles 15 in the HGN trunk 14including those unwanted fascicles, whereas bipolar stimulation resultsin a more specific and confined electrical field that will tend torecruit only the targeted fascicles 15 in the HGN trunk 14. Thus, thefascicles 15 in the HGN trunk 14 that innervate the tongue protrusormuscles can be more selectively activated via bipolar stimulation.Because the electrode contacts 82 will circumferentially surround theHGN trunk 14, the electrical field generated by the nerve cuff electrode10 in the bipolar stimulation mode can be selectively steered around theHGN trunk 14 to recruit the desired fascicles 15 within the HGN trunk14. It is further noted that, because the fascicles 15 innervating thetongue protrusor muscles sometimes, depending on the individual anatomy,may be more peripherally located within the nerve bundle that is locatedat the proximal position 20 to the HGN branches 24, it is desirable thatadjacent electrode contacts 82 can be activated in the bipolararrangement, such that the electrical field extends only peripherallyinto the HGN trunk 14.

Thus, with reference to FIG. 6, it may be desirable to activateelectrode contact pair 82 a-82 b, electrode contact pair 82 b-82 c,electrode contact pair 82 c-82 d, electrode contact combination 82 d-82e, electrode contact combination 82 e-82 f, or electrode combination 82f-82 a. As shown in FIG. 6, electrode combination 82 a-82 b, whenactivated, create a confined bipolar electrical field therebetween thatrecruits one or more of the peripheral, less centrally located fascicles15 a, as opposed to recruiting the more centrally located fascicles 15b. Of course, any of the other electrode contact combinations can beoperated in a bipolar manner to recruit other peripherally locatedfascicles 15 a. The first one of the electrode contacts 82 in thecombination can be a cathode, and the second one of the electrodecontacts 82 in the combination can be an anode, or vice versa. There areother possible electrode contact combinations or contact sets that canbe possibly chosen, which are described later in this disclosure inrelation to titrating and fitting electrode contacts to determine theoptimal set(s).

Notably, the strongest electrical field generated by the nerve cuffelectrode 10 will be beneath an active electrode contact/cathode. Thus,in order to effectively employ bipolar stimulation, the nerve cuffelectrode 10 may have the following design constraint: L≥2W, where W isthe width of each electrode contact 82, and L is the center-to-centerdistance between two adjacent electrode contacts 82, as illustrated inFIG. 5. This constraint is based on the commercial needs inneuromodulation therapies to cover the most distance with spatialseparations L and using the fewest number of electrode contacts 82. Thewidth of the electrode contacts 82 will typically be based on theparticular neural element that will be stimulated or the size of thecuff body 80, or a combination thereof, and will set the strength rangesof the electric fields generated by the nerve cuff electrode 10. As thecenter-to-center distance L exceeds the L≥2W design constraint, theelectric field generated by a bipolar pair of electrode contacts 82quickly starts to resemble a monopolar electric field as if there was aremote anode (unless there is a dramatic increase in the electric fieldamplitude). The ability to perform current steering between two or moreadjacent electrode contacts 82 also weakens. In contrast, if adjacentelectrode contacts 82 are too close or touching each other, there may bebleeding of electrical fields across the active contacts 82 at a higheramplitude, thereby creating a short that reduces the ability tospatially select fascicles. Thus, it is important that thecenter-to-center distance L between adjacent electrode contacts 82 andthe width W of the electrode contacts 82 be constrained.

To maintain the distance between the electrode contacts 82 a, 82 f inaccordance with the L≥2W design constraint over a variety of differentnerve sizes, thereby ensuring that bipolar stimulation using theelectrode contacts 82 a, 82 f is effective, the nerve cuff electrode 10may optionally be designed in the manner described in U.S. ProvisionalPatent Application Ser. No. 62/552,266, entitled “Stimulator Systems andMethods or Selectively Recruiting Fascicles in Hypoglossal Nerve Trunk,”which is expressly incorporated herein by reference.

The stimulation energy generated by the stimulation circuitry 68 takesthe form of a train of electrical pulses under control of the controlcircuitry 70. The electrical pulse train may be set to a constant timeduration or it may be adaptive, meaning that duration of the train ofpulses can change dynamically based on a predictive algorithm thatdetermines the duration of the inspiratory phase of the respiratorycycle.

Referring now to FIG. 7, various electrical pulse trains that can begenerated by the stimulation circuitry 76 will now be described. In oneembodiment illustrated in FIG. 7a , an electrical pulse train comprisesa single stimulation pulse S1 or S2. The stimulus pulse S1 or S2 hasstimulus parameters: stimulus pulse width, the stimulus pulse current orvoltage amplitude, and stimulus frequency. The frequency determines thetime duration between two consecutive pulses S1, S2. These multiplestimulus pulses may also be called a “train” of pulses or a “burst” ofpulses. Usually there is a quiescent period, as shown in FIG. 7d ,between two trains or burst of stimulus pulses, in this case, betweenstimulation pulses S6-S9 and S10. During this quiescent time, there isno stimulation occurring. The stimulus pulses can be cathodic (upperY-axis direction in FIG. 7) or anodic (lower Y-axis direction in FIG.7). The stimulus could be bi-phasic, and symmetric (FIG. 7b ), meaningthe electrical charge in the cathodic direction and anodic direction ofa single pulse S3 are the same. Sometimes stimulation pulses S4, S5 canbe bi-phasic, charge-balanced, but not symmetric (FIG. 7c ). Thecathodic amplitude is greater than the anodic amplitude, but the totalcharge delivered out through an electrode contact during the cathodicphase is balanced by the same quantity of electrical charge incominginto the same electrode contact. Area C equals area D and area E isequal to area F. A stimulus that is charge-balanced is desirable inorder to ensure that the electrode contacts do not erode prematurelyduring chronic implantation. For example, a charge-unbalanced cathodicpulse as shown in FIG. 7a can stimulate a nerve, but is not a desirablestimulus choice for an IPG. Although it is possible to elicit nervestimulation using an anodic pulse, a cathodic pulse is generally used tostimulate a nerve, since the nerve stimulation threshold (stimulusamplitude that just triggers nerve conduction) needed is much lower witha cathodic pulse than an anodic pulse.

Referring now to FIG. 8, shows a train of biphasic, charge-balancedpulses comprising initial pre-conditioning pulses, designated by X,followed by larger amplitude stimulus pulses, designated by Y, which areat a higher amplitude compared to the pre-conditioning pulses. Both Xand Y stimuli may be charge-balanced. The X preconditioning pulses maybe as low as 10% and more typically 50-90% of the Y stimulus pulses.This particular stimulation pattern can be used to “precondition” theperipheral, less centrally located nerve fascicles 15 a (i.e., the nervefascicles closer to the outer circumference of the HGN trunk 14) overthe more centrally located nerve fascicles 15 b (i.e., the nervefascicles closer to the center of the HGN trunk 14), as shown in FIG. 6.Although it is a general assumption that it is the peripherally locatedtarget fascicles 15 a that innervate the tongue protrusor muscles, it isdependent on individual anatomy and the target fascicles may in fact bemore centrally located in the HGN trunk. Thus, the usefulness ofpreconditioning will depend on the anatomy of an individual and thelocation of the target nerve fascicles in relation to the center of thenerve bundle. Preconditioning, as described, is a therefore astimulation tool that may be optionally applied depending oncircumstances.

In operation, the initial pre-conditioning pulses X at the loweramplitude will stimulate the more peripherally located nerve fascicles15 a of the HGN trunk 14. This causes these nerve fascicles to be“pre-conditioned,” so that they are not inclined to be stimulated laterby a larger amplitude stimulation pulses Y. The lower amplitudepre-conditioning pulses X are low enough in amplitude that they will notstimulate the more centrally located nerve fascicles 15 b of the HGNtrunk 14. While the peripherally located nerve fascicles 15 a of the HGNtrunk 14 are in their “pre-conditioned” state and not excitable, thelarger amplitude stimulation pulses Y will reach into the center of theHGN trunk 14 with sufficient charge density to stimulate and activatethe more centrally located nerve fascicles 15 a.

Thus, in the case where the more centrally located nerve fascicles 15 bof the HGN trunk 14 happen to innervate the tongue protrusor muscles,this preconditioning stimulation pattern can provide selectivestimulation of these centrally located nerve fascicles 15 b withoutstimulating nerve fascicles that innervate other extraneous muscles,namely the peripherally located nerve fascicles 15 a. In otherembodiments, instead of increasing the stimulus amplitude in the latterpart of pulse train Y, another possible way of achieving higherelectrical charge intensity to activate the centrally located nervefascicles 15 b of the HGN trunk 14 is to, relative to thepre-conditioning pulses, increase stimulus pulse width, increasefrequency of stimulation, or provide some combination thereof. It shouldbe appreciated that the use of the preconditioning stimulation patternis not limited to HGN trunks 14, but can be used with any nerve trunkwhere it is desirable to selectively stimulate more centrally locatedfascicles over more peripherally located nerve fascicles.

Thus, selective targeting of the tongue protrusor muscles can beachieved by spatially stimulating the fascicles innervating these tongueprotrusor muscles by selectively using the electrode contacts 82 of thenerve cuff electrode 10 to stimulate the HGN trunk 14. Furthermore, byusing lower amplitude pre-conditioning pulses to desensitize thefascicles innervating the tongue retractor muscles, followed by acathodic stimulation to target the fascicles innervating the tongueprotrusor muscles, even better targeting of the tongue protrusor musclescan be achieved in the case where the fascicles innervating the tongueprotrusor muscles are deeper in the HGN trunk 14. Thus, it can beappreciated from the foregoing that the combination of several electrodecontacts 82 on the nerve cuff electrode 10 that provide multipleindependent electrode channels and the pre-conditioning stimulationtrains provides a margin for placement of the nerve cuff electrode 10 onthe HGN trunk 14 and variation in the surgical approach across varioussurgeons.

Having described the arrangement and function of the stimulation system10, one embodiment of a method of using the stimulation system 10 totreat OSA in a patient will now be described with reference to FIG. 9.

First, the electrode contacts 82 are circumferentially disposed aroundthe HGN trunk 14. In particular, the cuff body 80 is maintained in theunfurled state (FIG. 5) while placing the cuff body 80 around the HGNtrunk 14 (step 102). For example, the unfurled cuff body 80 may beplaced underneath the HGN trunk 14. The cuff body 80 may be maintainedin the unfurled state by, e.g., holding it open, although the cuff bodywill tend to return to its furled, resting state. The HGN trunk 14 mayhave a diameter, e.g., typically in the range of 2.5 mm to 4.0 mm.

Next, the cuff body 80 is transitioned from the unfurled state into thefurled state (FIG. 6), such that the cuff body 80 wraps around the HGNtrunk 14 (step 104). The cuff body 80 may be placed from the unfurledstate into the furled state by letting go of both ends of the cuff body80, such that the cuff body 80 automatically transitions from theunfurled state to the furled state. The electrode contacts 82 preferablycircumferentially span at least a 180-degree arc around the HGN trunk14, and more preferably, at least a 270-degree arc around the HGN trunk14. Preferably, the center-to-center spacing L of each pair of adjacentones of the electrode contacts 82 is equal to or less than twice thewidth W of each electrode contact of the respective pair of adjacentelectrode contacts 82.

Next, the IPG 52 is implanted within the patient (step 106), and theproximal lead connector 62 is mated with the receptacle 64 of the IPG 52(step 108). Next, the system 50 is titrated to determine at least oneelectrode contact 82 (an “electrode contact set”) that provides the besttreatment of the OSA by delivering electrical stimulation energy todifferent electrode contact sets 82 to determine the optimal electrodecontact set(s) (step 110). For example, electrode contact set 82 may beselected, an electrical pulse train may be delivered to the selectedelectrode contact set to stimulate the HGN trunk 14, and preferably, thefascicles of the HGN trunk 14 innervating the tongue protrusor muscles,and then repeated for all possible electrode sets to determine theoptimal electrode contact set(s). Further details of several techniquesfor titrating the neurostimulation system 10 are discussed below. In onemethod, each electrode contact set comprises a pair of adjacent ones ofthe electrode contacts 82, in which case, the pairs of electrodecontacts are selected for delivery of the electrical pulse trains in abipolar mode. In another method, each electrode contact set comprises asingle electrode contact 82, in which case, individual ones of theelectrode contacts 82 are selected one at a time for delivery of theelectrical pulse trains in a monopolar mode.

Initially, in order to trigger a peripherally located fascicle orfascicles 15 a innervating the tongue protrusor muscles, all of theelectrode contact sets may be tested using regular, constant amplitudepulse trains having a defined pulse duration and frequency, as shown inFIG. 7. If no peripherally located fascicle 15 a innervating the tongueprotrusor muscles is triggered, all of the electrode contact sets may betested using pre-conditioning pulse trains, such as that shown in FIG.8, in order to trigger any centrally located fascicle or fascicles 15 bthat may possibly innervate the tongue protrusor muscles.

Once an optimal electrode contact set (or sets) is determined, the IPG52 is programmed to the selected optimal electrode contact set (or sets)using the clinician programmer 56 (step 112). The IPG 52 can be turnedon with the clinician programmer 56 or the patient programmer 58. Or,the patient can turn the IPG 52 to an ON setting, e.g., by tapping thearea of the body over the implanted IPG 52 multiple times in quicksuccession or by using the patient programmer 64 (step 114). The IPG 52may be turned ON when the patient wishes to sleep, or OFF, when thepatient is awake during the day. In the ON position, the IPG 52 willprovide, through the selected electrode contact or contacts, a stimulustrain (or stimulus burst) at the programmed setting. Stimulation willmove the tongue forward while the patient is asleep, so that during anyobstructive apneic event, the patient will not be prevented frombreathing. As such, when the IPG 52 is in the ON position, a train ofpulse stimulation occurs at every breathing inspiration.

To save battery power, the IPG 52 may only provide therapy under aspecific set of circumstances, e.g., if the patient is sleeping in anapneic position. To this end, the IPG 52 may determine if the patient isin an apneic position by measuring an orientation of the body of thepatient (step 116), and if so, then determine if the patient is sleepingby measuring a physiological parameter indicative of whether the patientis sleeping (step 118).

If the patient is sleeping in an apneic position, the physiologicalartifacts caused by respiration are sensed and stored (step 120), thenext projected onset of an inspiratory phase of the respiratory cycle isdetermined based on the sensed physiological artifacts (step 122), andelectrical stimulation energy (e.g., an electrical pulse train) isdelivered to the programmed electrode contact set in synchronizationwith a respiratory cycle based on the sensed physiological artifacts,and in particular, immediately before, at, or right after the nextprojected onset of the inspiratory phase of the respiratory cycle (step124), thereby treating the OSA.

If the electrical pulse train is conventional in nature, one or moreperipherally located nerve fascicles 15 a in the HGN trunk 14(presumably, the peripherally located nerve fascicle(s) 15 a adjacent tothe programmed electrode contact set) are triggered. If the electricalpulse train is a pre-conditioning pulse train, one or more peripherallylocated nerve fascicles 15 a in the HGN trunk 14 will bepre-conditioned, and rendered not excitable, by the initialpreconditioning current or voltage amplitude, while one or morecentrally located nerve fascicles 15 b in the HGN 14 will betriggered/activated by the subsequently delivered higher stimulatingcurrent or voltage amplitude.

Referring now to FIG. 10, another embodiment of a stimulation system 50′that selectively stimulates the fascicles of the trunk 14 of the HGN 12that innervate the tongue protrusor muscles for treating OSA will now bedescribed. The stimulation system 50′ is similar to the stimulationsystem 50′ illustrated in FIG. 2, with the exception that thestimulation system 50′ additionally comprises a feedback mechanism 90that can titrate stimulation system 50′ in a clinical setting in orderto provide chronic therapy to a patient suffering from OSA.

The feedback mechanism 90 of the system 50 is capable of sensing aphysiological parameter indicative of the efficacy in treating apatient's obstructive sleep apnea. In conjunction with the feedbackmechanism 90, the clinician programmer 56 can be used to determine thebest set or sets of electrode contacts 82, along with other stimulationparameters (e.g., stimulation pulse amplitude, stimulation pulse width,stimulation pulse frequency, and number of stimulus pulses in a pulsetrain, or burst and frequency of the stimulation pulses), that optimallyrecruits the target fascicles of the HGN trunk 14 that controls theprotrusor muscle which moves the tongue forward.

The system 50′ can be titrated the first time right after implantationof the nerve cuff electrode 10 or during clinical follow-up sessions.The system 50′ can also be titrated during the implantation surgeryitself, during a traditional sleep study, a drug induced sleep study, orother appropriate setting. The system 50′ can be titrated while thepatient is asleep, or it could be performed sometimes with the patientawake.

The clinician programmer 56 may be operated to iteratively testdifferent sets of electrode contacts 82 of the nerve cuff electrode 10to determine the set or sets electrode contacts 82, along with thecorresponding types of electrical pulse trains, that provides the besttherapy for treating the OSA of the patient. For the purposes of thispatent disclosure, a set of electrode contacts 82 may include only oneelectrode contact 82 or may include multiple electrode contacts 82.

As an example, using an asymmetrical (peak cathodic amplitude largerthan peak anodic amplitude), biphasic, charge-balanced, stimulus such asshown in FIG. 7(c) and referring to FIG. 5 or FIG. 6, the electrodecontact 82 selected could be a monopolar set, with the outer case 66 ofthe IPG 52 turned on as indifferent, return electrode contact. Then eachelectrode contact, 82 a, 82 b, 82 c, 82 d, 82 e, and 82 f can be testedfor successively for its efficacy.

Sometimes a monopolar stimulation can have two stimulating (functioningcathodic) electrode contacts 82, e.g., the outer case 66 of the IPG 52functions as the indifferent electrode (anode), electrode contact 82 aand electrode contact 82 b concurrently function as stimulatingcathodes. In this latter arrangement, using two stimulating cathodesconcurrently, true current steering can be accomplished. For example, ifelectrode contact 82 a outputs 50% of the total current while, at thesame time, electrode contact 82 b outputs 50% of the total current, thenet effect is to create a virtual electrode that appears to be anelectrode contact that is positioned right in between the two electrodecontacts, 82 a and 82 b. In other cases, the current output may beuneven, for example 70% of total current output for contact 82 a and 30%of total current output from contact 82 b. In that case the virtualelectrode will be in between but closer to contact 82 a than 82 b.Current steering means that the center of electrical current density issomewhere between the centers of two adjacent electrodes and is anextremely powerful tool to “steer” the stimulation precisely between twoelectrode contacts.

In addition, the titration or fitting may test various sets of electrodecontacts in bipolar stimulation mode. Examples of bipolar modes include:(A) 82 a (stimulating cathode) and 82 b (functioning anode); (B) 82 a(stimulating cathode) and 82 c (functioning anode); and (C) threeelectrode contacts in a tripolar arrangement, but still bipolarstimulation —82 b (cathode), 82 a (return anode) and 82 c (returnanode). Note there are opportunities for field shaping because 82 a and82 c may both return 50% of the total current output from contact 82 b.Alternatively, contacts 82 a and 82 c could sink different values of thetotal current, e.g. 40% and 60%. Of course, contact 82 b has athroughput of 100% of the stimulating current at any instant in time. Asthe numbers of electrode contact increase, e.g. six electrode contacts,there are many combinations of electrode contacts that can be used,hence the need for a fitting or titrating step to choose an optimal setof electrode contacts, bipolar or monopolar stimulation, and stimulusamplitudes of individual contacts.

The clinician programmer 56 may automatically or manually cycle througheach possible set of electrode contacts 82, score the set of electrodecontacts 82, along with the electrical pulse train types, based on theoutput of the feedback mechanism 90, and select the best set or sets ofelectrode contacts 82 and electrical pulse trains based on thecorresponding efficacy scores.

The efficacy of the selected set of electrode contacts 82, along withthe corresponding electrical pulse train types, can be quantified usinga scoring system, e.g., by assigning a score from 1 to 100 to theselected set of electrode contacts 82 and corresponding stimulationparameters, with 1 being the least effective, and 100 being the mosteffective. The clinician programmer 56 may apply a preset series ofstimulation patterns for each of the sets of electrode contacts 82,while utilizing the feedback mechanism 90 to score the effectiveness ofthe settings. The clinical programmer 56 may use algorithms thatrecursively apply test stimulation patterns based upon earlier computedscores to converge on the optimal settings for a given patient.

If monopolar stimulation is assumed, different electrode contacts 82 maybe selected in combination with the outer case 66, which serves as thereturn electrode contact. For example, if the nerve cuff electrode 10has four electrode contacts labeled, #1, #2, #3, and #4, along with theouter case 66 as the first electrode contact, electrode contact #1 canbe selected and tested, then electrode contact #2 can be selected andtested, then electrode contact #3 can be selected and tested, and thenelectrode contact #4 can be selected and tested. Of course, variouscombinations of electrode contacts can be tested. For example, alongwith the outer IPG case 66 as the indifferent or return electrodecontact, electrode contact combination #1, #2 can be selected andtested, electrode contact combination #2, #3 can be selected and tested,electrode contact combination #3, #4 can be selected and tested, andelectrode contact combination #3, #4 can be selected and tested. Ifbipolar stimulation is assumed, pairs of electrode contacts 82 may beselected. For example, twelve total bipolar, two electrode contactcombinations can be selected—noting pair #1, and #4 can be differentthan #4 and #1, depending on which electrode contact 82 is functioningmainly as the active, stimulating contact.

The feedback mechanism 90 can take the form of any mechanism that canoutput a signal indicative of the efficacy of the treatment of OSA.Generally, during titration, the patient is either asleep or undergeneral anesthesia. In one embodiment, the feedback mechanism 90comprises a temperature sensor that can be located under the nose and/orclose to the mouth of the patient to measure the temperature of theinhaled and exhaled air of the patient. Since inhaled air has a lowertemperature than that of the exhaled air, the temperature of the inhaledand exhaled air is a good indicator of the respiratory cycle. Thetemperature change between the inhaled air and the exhaled air is bestillustrated in FIG. 11, which shows an approximate ±2° K peak-to-peakdifference in temperature between air inhaled through the nose and airexhaled from the nose. Thus, based on the signal output by thetemperature sensor, the clinician programmer 56 can determine thebeginning and ending of each inspiration phase in the respiratory cycle,as well as the efficiency of the inspiration phase (i.e., whether thepatient is taking a full breath during the inspiration phase).

Based on this, the clinician programmer 56 can compute a score of thetherapy provided by the current set up of the system 50, and inparticular, the currently selected set of electrode contacts andcorresponding stimulation parameters. For example, if the valleys of thesignal output by the temperature sensor indicate a regular and normalpattern of inspiration during the respiratory cycle, the therapy scoreassigned to the current set up may be relatively high, whereas if thevalleys of the signal output by the temperature sensor indicate anon-regular or abnormal pattern of inspiration during the respiratorycycle, the therapy score assigned to the current set up may berelatively low. Thus, the more efficient the inspiration phase of therespiratory cycle, the higher the therapy score, and the less efficientthe inspiration phase of the respiratory cycle, the lower the therapyscore.

In another embodiment, the feedback mechanism 90 comprises a carbondioxide (CO2) sensor that can be located under the nose and/or close tothe mouth of the patient to measure the concentration of CO2 in theinhaled and exhaled air of the patient. Since inhaled air has a lowerCO2 concentration than that of the exhaled air, the CO2 concentration ofthe inhaled and exhaled air is a good indicator of the respiratorycycle. The CO2 concentration change between the inhaled air and theexhaled air is best illustrated in FIG. 12, which shows an approximate±85 ppm peak-to-peak difference in CO2 concentration between air inhaledthrough the nose and air exhaled from the nose. Thus, based on thesignal output by the CO2 sensor, the clinician programmer 56 candetermine the beginning and ending of each inspiration phase in therespiratory cycle, as well as the efficiency of the inspiration phase(i.e., whether the patient is taking a full breath during theinspiration phase).

In a similar manner described above with respect to the temperaturesensor, the clinician programmer 56 can compute a score of the therapyprovided by the current set up of the system 50, and in particular, thecurrently selected set of electrode contacts and correspondingstimulation parameters. That is, if the valleys of the signal output bythe CO2 sensor indicate a regular and normal pattern of inspirationduring the respiratory cycle, the therapy score assigned to the currentset up may be relatively high, whereas if the valleys of the signaloutput by the CO2 sensor indicate a non-regular or abnormal pattern ofinspiration during the respiratory cycle, the therapy score assigned tothe current set up may be relatively low. Thus, the more efficient theinspiration phase of the respiratory cycle, the higher the therapyscore, while the less efficient the inspiration phase of the respiratorycycle, the lower the therapy score.

In still another embodiment, the feedback mechanism 90 comprises one ormore electro-myographic (EMG) sensors that measure the electricalpotential generated by the muscle cells of the tongue in response toelectrical stimulation of the HGN 12. The EMG sensor(s) may beincorporated into an oral appliance or mouth guard (not shown), suchthat the EMG sensor(s) is in surface contact with the appropriatemuscle(s) of the tongue when the oral appliance or mouth guard is wornby the patient, or the EMG sensor(s) can take the form of needleelectrodes that can be placed into the appropriate muscle(s) of thetongue. Alternatively, non-invasive EMG sensor(s) may be placed on theneck region of the patient to detect movement of the tongue caused bythe electrical stimulation of the HGN.

Based on the EMG signals output by the EMG sensor(s), the clinicianprogrammer 56 can compute a score of the therapy provided by the currentset up of the system 50, and in particular, the currently selected setof electrode contacts and corresponding stimulation parameters. That is,the EMG activity sensed by the EMG sensor(s) in synchronization with thestimulation of the HGN 12 is indicative of activation of the tongueprotrusor muscles. If the magnitude of the EMG activity is relativelyhigh, indicating a strong activation of the tongue protrusor muscles,the therapy score assigned to the current set up may be relatively high,whereas if the magnitude of the EMG activity is relatively low,indicating no or weak activation of the tongue protrusor muscles, thetherapy score assigned to the current set up may be relatively low.

In still another embodiment, the feedback mechanism 90 comprises acamera that captures pictures of the airway of the patient, therebyproviding an indication of how well the obstruction in the airway of thepatient is eliminated in response to electrical stimulation of the HGN12. The camera may be on the end of an endoscope typically insertedthrough the nasal cavity. The clinician programmer 56 may have imageanalysis software that computes the area of the airway opening shown inthe picture provided by the camera, and based on this computed area,computes a score of the therapy provided by the current set up of thesystem 50, and in particular, the currently selected set of electrodecontacts and corresponding stimulation parameters. Thus, if the computedarea of the airway opening is relatively large, the therapy scoreassigned to the current set up may be relatively high, whereas if thecomputed area of the airway opening is relatively low, the therapy scoreassigned to the current set up may be relatively low.

In yet another embodiment, the feedback mechanism 90 comprises aninertial sensor (e.g., an accelerometer or gyroscope) that measures themovement of the tongue in response to electrical stimulation of the HGN12. The inertial sensor may be incorporated into an oral appliance ormouth guard (not shown). Based on the signals output by the inertialsensor, the clinician programmer 56 can compute a score of the therapyprovided by the current set up of the system 50, and in particular, thecurrently selected set of electrode contacts and correspondingstimulation parameters. That is, the motion activity sensed by theinertial sensor in synchronization with the stimulation of the HGN 12 isindicative of movement of the tongue. If the magnitude of the signals isrelatively high, indicating a strong activation of the tongue protrusormuscles, the therapy score assigned to the current set up may berelatively high, whereas if the magnitude of the signals is relativelylow, indicating no or weak activation of the tongue protrusor muscles,the therapy score assigned to the current set up may be relatively low.

Referring now to FIG. 13, one embodiment of the method 150 of fitting ortitrating the system 10 to a particular patient in a clinical setting inorder to subsequently provide chronic therapy will be described. By“fitting” or “titrating” is meant herein the identification andselection of an optimal set of electrode contacts, selection ofmonopolar or bipolar stimulation, the determination of stimulusparameters, e.g., amplitude, frequency, pulsewidth, and whether to applypreconditioning pulses. Advantageously, once the nerve cuff electrode 10is implanted within the patient, and in an embodiment of the method,around the trunk portion 14 of the HGN 12 of the patient, embodiments ofthe fitting procedure will aid in identifying the preferred electrodecontact or contacts of the nerve cuff electrode 10 to use in order tooptimally recruit the fascicles of the HGN trunk 14 that innervate themuscles that control protraction of the tongue. In this fittingprocedure, it is important also to avoid stimulating muscles thatcontrol tongue retraction. The fitting procedure may also be used to setthe stimulus parameters, e.g., stimulus pulse width, stimulus frequency,number of stimulus pulses in a pulse train, or burst and frequency ofthe stimulus pulses, and if a pre-conditioning stimulus pulse train isused, the fitting procedure may be used to determine the intensity ofthe stimulation pulses relative to the pre-conditioning pulses in termsof pulse amplitudes or pulse widths. The fitting procedure can also beused to initially determine whether a pre-conditioning pulse train isneeded at all, or whether a simple electrical pulse train withoutpre-conditioning will suffice to activate the desired fascicles in theHGN 12.

First, a set of electrode contacts 82 of the nerve cuff electrode 10 isselected (step 152), and the type of the electrical pulse train (e.g.,amplitude, pulse width, pulse duration, monopolar or bipolar mode,conventional or pre-conditioning, etc.)) generated by the system 50′will be selected (step 154). The electrical pulse train may be, e.g., aregular, constant amplitude pulse train having a defined train durationand frequency, such as that shown in FIG. 7, or a pre-conditioningelectrical pulse train, such as that shown in FIG. 8, and may be eitherbipolar or monopolar stimulation.

Then, the electrical pulse train is delivered to the selected electrodecontact(s), for example, 82 (a)-(f), in accordance with the selectedelectrical pulse parameters (step 156), and the intensity of thestimulation is adjusted (by adjusting pulse amplitude and/or pulsewidth) from below nerve stimulation threshold to slightly above nervestimulation threshold (step 158). Next, the efficacy of the selected setelectrode contacts 82 in treating the OSA of the patient is determined.

In particular, the feedback mechanism 90 senses a physiologicalparameter indicative of the efficacy of the currently selected set ofelectrode contacts 82 and corresponding set of stimulation parameters intreating the OSA of the patient (step 160). The clinician programmer 56then scores the set of electrode contacts 82, along with the set ofstimulation parameters, based on the output of the feedback mechanism 90(step 162). If all possible selections of electrical pulse trains forcurrently selected set of electrode contacts 82 have not yet been tested(step 164), the clinician programmer 56 returns to step 154, where adifferent set of stimulation parameters is selected for the currentlyselected electrode contact set, and steps 156-164 are repeated. If alltypes of electrical pulse trains for the currently selected set ofelectrode contacts 82 has been tested (step 164), and if not allpossible electrode sets of electrode contacts 82 have been tested (step166), the fitting procedure returns to step 152, where a different setof electrode contacts 82 is selected and tested by repeating steps154-166. If all possible electrode sets of electrode contacts 82 havebeen tested (step 166), the clinician, using the clinician programmer 56selects the best set or sets of electrode contacts 82 and correspondingtype of electrical pulse train, preferably, those with the best therapyscore(s) (step 168), and programs the IPG 52 with the best set or setsof electrode contacts 82 and corresponding types of electrical pulsetrains (step 170).

Although particular embodiments of the present inventions have beenshown and described, it will be understood that it is not intended tolimit the present inventions to the preferred embodiments, and it willbe obvious to those skilled in the art that various changes andmodifications may be made without departing from the spirit and scope ofthe present inventions. Thus, the present inventions are intended tocover alternatives, modifications, and equivalents, which may beincluded within the spirit and scope of the present inventions asdefined by the claims.

What is claimed is:
 1. A method of titrating a neurostimulation systemthat treats obstructive sleep apnea (OSA), comprising: circumferentiallydisposing a plurality of electrode contacts around a trunk of ahypoglossal nerve (HGN); sequentially delivering an electrical pulsetrain to each of a plurality of sets of the electrode contacts;measuring a physiological parameter of the patient indicative of anefficacy of the delivered electrical pulse train in treating the OSA;and selecting one of the sets of electrode contacts based on themeasured physiological parameter.
 2. The method of claim 1, wherein theelectrical pulse train is delivered from a neurostimulator, the methodfurther comprising programming the neurostimulator with the selected setof electrode contacts.
 3. The method of claim 1, wherein the HGN trunkhas a diameter in the range of 2.5 mm to 4.0 mm.
 4. The method of claim1, wherein the plurality of electrode contacts comprises at least threeelectrode contacts.
 5. The method of claim 1, wherein the plurality ofelectrode contacts comprises at least six electrode contacts.
 6. Themethod of claim 1, wherein the plurality of electrode contactscircumferentially span at least a 180-degree arc around the HGN trunk.7. The method of claim 1, wherein the plurality of electrode contactscircumferentially span at least a 270-degree arc around the HGN trunk.8. The method of claim 1, wherein a center-to-center spacing of eachpair of adjacent ones of electrode contacts is equal to or less thantwice the width of each electrode contact of the respective pair ofelectrode contacts.
 9. The method of claim 1, wherein each set ofelectrode contacts comprises a pair of adjacent ones of the electrodecontacts, and the electrical pulse train is sequentially delivered toeach set of electrode contacts in a bipolar mode.
 10. The method ofclaim 1, wherein each set of electrode contacts comprises a singleelectrode contact, and the electrical pulse train is sequentiallydelivered to each set of electrode contacts in a monopolar mode.
 11. Themethod of claim 1, wherein the electrical pulse train has an initial,preconditioning current or voltage amplitude and a subsequent higherstimulating current or voltage amplitude, such that one or moreperipherally located nerve fascicles in the nerve are pre-conditioned bythe initial preconditioning current or voltage amplitude, and one ormore centrally located nerve fascicles in the nerve further away fromthe at least one electrode than the peripherally located nerve fasciclesare triggered by the higher stimulating current or voltage amplitude,while the one or more pre-conditioned peripherally located nervefascicles are not triggered by the higher stimulating current or voltageamplitude.
 12. The method of claim 1, wherein the physiologicalparameter comprises one or more of the temperature of inhaled andexhaled air of the patient, the concentration of CO2 in inhaled andexhaled air of the patient, the electrical potential generated by themuscle cells of a tongue of the patient, a picture of the airway of thepatient, and the movement of the tongue of the patient.
 13. The methodof claim 12, wherein the physiological parameter comprises thetemperature of inhaled and exhaled air of the patient.
 14. The method ofclaim 12, wherein the physiological parameter comprises theconcentration of CO2 in inhaled and exhaled air of the patient.
 15. Themethod of claim 12, wherein the physiological parameter comprises theelectrical potential generated by the muscle cells of a tongue of thepatient.
 16. The method of claim 12, wherein the physiological parametercomprises a picture of the airway of the patient.
 17. The method ofclaim 12, wherein the physiological parameter comprises the movement ofthe tongue of the patient.
 18. The method of claim 1, further comprisingcomputing a score of each of the electrode contact sets based on therespective measured physiological parameter.
 19. The method of claim 18,further comprising determining the efficiency of each inspiration phasein the respiratory cycle based on the measured physiological parameter,and computing the score based on the determined efficiency of eachinspiration phase in the respiratory cycle.
 20. The method of claim 18,wherein the measured physiological parameter comprises a peak-to-peakdifference in temperature of inhaled and exhaled air of the patient, themethod further comprises determining the efficiency of each inspirationphase in the respiratory cycle based on the measured peak-to-peakdifference in temperature of inhaled and exhaled air of the patient,wherein the score is computed based on the determined efficiency of eachinspiration phase in the respiratory cycle.
 21. The method of claim 18,wherein the measured physiological parameter comprises a peak-to-peakdifference in the concentration of CO2 in inhaled and exhaled air of thepatient, the method further comprises determining the efficiency of eachinspiration phase in the respiratory cycle based on the measuredpeak-to-peak difference in the concentration of CO2 in inhaled andexhaled air of the patient, wherein the score is computed based on thedetermined efficiency of each inspiration phase in the respiratorycycle.
 22. The method of claim 18, wherein the measured physiologicalparameter comprises an electrical potential generated by the musclecells of a tongue of the patient, the method further comprisingdetermining the extent to which one or more tongue protusor muscles areactivated based on the measured electrical potential generated by themuscle cells of a tongue of the patient, wherein the score is computedbased on the determined extent to which the one or more tongue protrusormuscles are activated.
 23. The method of claim 18, wherein the measuredphysiological parameter comprises a picture of the airway of thepatient, the method further comprising determining the extent to whichthe airway of the patient is obstructed based on the picture of theairway of the patient, wherein the score is computed based on thedetermined extent to which the airway of the patient is obstructed. 24.The method of claim 18, wherein the measured physiological parametercomprises a movement of the tongue of the patient, the method furthercomprising determining the extent to which the tongue of the patientprotrudes based on the movement of the tongue of the patient, whereinthe score is computed based on the determined extent to which the tongueof the patient protrudes.
 25. The method of claim 1, wherein theelectrode contacts are located on the HGN trunk proximal to a medialbranch of the HGN trunk.